Immune modulation device for use in animals

ABSTRACT

The present invention is directed to an implantable immune modulation device that is useful for modulating an immune response in mammals, comprising a plurality of fibers, within a porous shell. The fiber filling is loaded with single or multiple antigens, and optionally one or more biologically active compounds such as cytokines (e.g. lymphokines, chemokines etc.), attachment factors, genes, peptides, proteins, nucleotides, carbohydrates or cells depending on the application.

This application claims benefit of provisional patent application No.60/290,542 filed May 11, 2001, which is hereby incorporated by referenceherein.

FIELD OF THE INVENTION

The present invention relates to an implantable device and method formodulating the immune response to antigens in mammals. More specificallythe present invention provides a porous, implantable device containing afibrous support and at least one antigen. This device may be used tomodulate the immune system to provide a robust response against anantigen, or to down regulate an existing response.

BACKGROUND OF THE INVENTION

Induction of an immune response to an antigen and the magnitude of thatresponse depend upon a complex interplay among the antigen, varioustypes of immune cells, and co-stimulatory molecules including cytokines.The timing and extent of exposure of the immune cells to the antigen andthe co-stimulatory milieu further modulate the immune response. Withinthe body, these various cell types and additional factors are broughtinto proximity in lymphoid tissue such as lymph nodes. Of the numerouscell types involved in the process, antigen-presenting cells (APC), suchas macrophages and dendritic cells, transport antigen from the peripheryto local, organized lymphoid tissue, process the antigen and presentantigenic peptides to T cells as well as secrete co-stimulatorymolecules. Thus, if antigen reaches lymph organs in a localizedstaggered manner, presenting antigenic epitopes, under the optimalconcentration gradient and under the appropriate environment comprisingco-stimulatory molecules, a response is induced in the draining lymphnode.

In this manner, a foreign antigen introduced into the body, such as bymeans of a vaccination, may or may not result in the development of adesirably robust immune response. Antigens used for vaccination includeattenuated and inactivated bacteria and viruses and their components.The success of vaccination depends in part on the type and quantity ofthe antigen, the location of the site of immunization, and the status ofthe immune system at the time of vaccination. Not all antigens areequally immunogenic, and for poorly immunogenic antigens, there are fewalternatives available to increase the effectiveness of theimmunization. Whereas in experimental animals numerous techniques areavailable to enhance the development of the immune response, such asconjugating the antigen to a more immunogenic carrier protein orbiomolecule (e.g., keyhole limpet hemocyanin), or the use of adjuvantssuch as Freund's Adjuvant or Ribi. For human vaccinations suchtechniques and adjuvants are not available. Thus, numerous diseases thatwould otherwise be preventable by vaccination before exposure to theinfectious agent, or in the case of a therapeutic vaccine, that mayinduce the development of an effective immune response to an existingdisease-causing agent or cell, such as cancer, are not available to thepatient.

Sponge implant studies have been performed in mammals to assess theimmune cell population attracted to a foreign body, which produce whatis called a sterile abscess, and sponges prior to or after implantationhave been loaded with antigen to further study the attracted cellpopulation. Vallera et al. (1982, Cancer Research 42:397-404) implantedsponges containing tumor cells in mice to examine the composition ofcells attracted over a 16 day period, and found that at an early time,cytotoxic cell precursors were present, and cytotoxicity peaked at day16. Sponges containing tumor cells implanted in mice that had beenpreviously immunized with tumor cells showed a more rapid appearance ofcytotoxic cells in the sponge. In neither case did cells from thespleen, lymph nodes or peritoneum show cytotoxicity, which suggested ahighly localized response to the antigen in the sponge.Zangemeister-Wittke et al. (1989, J. Immunol. 143:379-385) injected atumor vaccine into sponges implanted in tumor-immune mice, and monitoredthe generation of a secondary immune response at the sponge site. Noaccompanying effect was apparent in lymph nodes adjacent to theimplanted sponge.

Other devices which overcome some of the limitations of sponges forimmunomodulation have been proposed. U.S. Pat. No. 4,919,929 teachesthat an antigen can be loaded into solid shaped particles, which slowlyrelease the antigen following implantation. This type of device isenvisaged to increase the antibody titers in the milk of mammals andthereby confer higher levels of immunity in those who consume it. WOapplication 93/17662 describes a device that consists of an imperviousmembrane surrounding a core, which is a gel loaded with atherapeutically active ingredient (including antigens). There is atleast one port in the impervious membrane that is capable of releasingthe active to the surroundings. The use of the membrane is shown to slowthe rate of release of the bioactive molecule (including antigens)relative to the gel alone. This device therefore primarily serves as areservoir for slow release and does not facilitate the interaction ofcells with the bioactive, which necessarily must occur outside of thedevice. In U.S. Pat. No. 4,732,155, a device is proposed where there isa reservoir that provides prolonged release of a chemoattractant, whichis surrounded by a web of fibers adjacent to the reservoir. Cells areattracted to the reservoir and become trapped in the fibrous web. Thisdevice is proposed for use in characterizing allergic and inflammatoryresponses to test compounds by allowing controlled exposure to thecompound and by trapping the cells that respond to it. This device bothincorporates a mechanism for prolonged exposure to an antigen as well asa mechanism to facilitate cellular interaction with the antigen. Theopen web of fibers in this device; however, does not enable localretention of the cytokines and chemokines being secreted by theresponding cells since an open web of fibers will not providediffusional resistance to soluble factors.

This design is improved upon in WO 99/44583 which proposes a porousmatrix which is housed in a perforated but otherwise imperviousmembrane. Antigen is loaded within the device and can be present eitheras native antigen or can be encapsulated in a slow releasing polymerthat provides prolonged presentation of the antigen. Specific cells areattracted to the device by diffusion of the antigen from theperforations in the device and are also able to enter the device throughthe perforations, but the membrane provides sufficient diffusionalresistance that cytokines secreted by cells become locally concentratedwithin the device. The high local densities of cells and cytokinesproduce a much more robust immune response than is seen with anuncontained matrix or with simple prolonged release to surroundingtissues.

The preferred embodiment of the device mentioned above envisages theporous matrix to be a sponge and the membrane to be a perforated tube.While very favorable immunomodulation is seen with the device, it isimpractical to miniaturize and manufacture in large quantities. Theprimary reason is that it is very difficult to load a porous sponge intotubing. Sponges, due to their low bulk densities are mechanically weakand tend to tear easily when subjected to the tensile and compressiveforces of loading into small diameter tubing. By reducing the bulkdensity, more favorable mechanical properties can be encountered howeverthe matrix does not contain sufficient porosity to attain high celldensities. In addition, it is very difficult to cut small cylindricalcores of porous sponges for loading into tubes. The reason is that thepoor mechanical properties of the porous sponge lead to tearing when thesize of the piece being cut becomes very small. Consequently, the deviceenvisaged in WO 99/44583 is only practical to make in diameters ofgreater than 1 mm. Implantation of such a large profile device requiresa very sizable needle or trochar that would be very painful and causesignificant local trauma to a patient. An additional problem with thisdevice design is that it would be difficult to economically manufacturein large quantities. The reason is that each piece of sponge would needto be individually cut and stuffed into the tube. This would be verydifficult to mechanize and perform rapidly.

Accordingly, it would be advantageous to provide an implantable deviceand method for modulating an immune response to specific antigens inmammals, similar in concept to the design described in WO 99/44583,whose filling preserves the porosity presented by a porous sponge, whichis essential for rapid cellular infiltration, yet overcomes themechanical frailties of a sponge.

SUMMARY OF THE INVENTION

The present invention is directed to an implantable immune modulationdevice that is suitable for use in modulating an immune response inmammals, comprising an impermeable shell having a plurality of pores andsaid impermeable biocompatible shell having an interior lumen, abiocompatible fibrous scaffolding being disposed within said interiorlumen. The fibrous scaffolding is loaded with single or multipleantigens and optionally one or more biologically active compounds suchas cytokines (e.g. lymphokines, chemokines etc.), non-cytokine leukocytechemotactic agents, attachment factors, genes, peptides, proteins,nucleotides, carbohydrates, or cells depending on the application. Theshell of the device preferably is made from a polymer whose glasstransition temperature is below physiologic temperature so that thedevice will minimize irritation when implanted in soft tissues. Theshell allows cell ingress but hinders diffusion of soluble molecules outof the device. This helps to concentrate cytokines (e.g. lymphokine andchemokines) secreted by cells which have entered the device in responseto loaded antigens and other cells which are present in the device. Thislocal concentration of cells and cytokines significantly enhances theimmune response relative to implantation of antigens with standardadjuvants. The fibrous scaffolding provides a scaffold for cells toreside on, process the antigens and interact.

Additional benefits of the fibrous scaffolding disclosed in thisinvention include ease of miniaturization of a device to diameters ofless than 1 mm, the possibility of rapid insertion into small diametertubing or even the ability to have tubing continuously extruded aroundthe matrix.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 is a perspective drawing of one embodiment of the immunemodulating device described herein.

FIG. 2 is a scanning electron micrograph of one embodiment of a texturedfiber suitable for use in the present invention made by the processdescribed in Example 1.

FIG. 3 is a perspective drawing of one embodiment of the immunemodulating device showing one end of the device being sealed.

FIG. 4 is a perspective drawing of one embodiment of the immunemodulating device showing a device that is crimped.

FIG. 5 is a perspective drawing of one embodiment of the immunemodulating device showing one end of the device being crimped andsealed.

DETAILED DESCRIPTION OF THE INVENTION

An immune modulation device is disclosed herein which allows for cellingress and concentration of cytokines secreted by cells. A perspectiveview of the immune modulation device is provided in FIG. 1. The immunemodulation device 2 is comprised of a shell 4 surrounding an interiorlumen 10. The shell 4 has pores 6 that extend from the outer surface 8to the interior lumen 10. The interior lumen will have a volume of atleast 1×10⁻⁸ cm³, preferably will be at least 3×10⁻⁸ cm³ and mostpreferably the size of the lumen will be sufficient to elicit thedesired immune response from the animal in which it is implanted (whichcan be determined by methods well known in the art such as ELISA). Theshell 2 may have a variety of three dimensional shapes (e.g.cylindrical, spherical, rectangular, rhomboidal, etc.). For example theshell 2 will generally have a longitudinal axis and a cross-section thatmay be circular, oval or polygonal. Preferred for ease of manufacture isa cylindrical shape. A cylindrically shaped immune modulation device 2is illustrated in FIG. 1. The ends of the cylindrically shaped immunemodulation device may be capped or left open as illustrated in FIG. 1.The outer surface 8 of the immune modulation device 2 is preferablyimpervious to cytokines and immune cells and has numerous pores 6 thatallow for the ingress and egress of immune cells. The number of pores 6will generally be less than 25 percent of the outer surface andpreferably will be less than about 10 percent of the outer surface. Thepores 6 size may range from about 10 to about 500 microns and preferablyin the range of from about 100 to about 400 microns. The interior 10 ofimmune modulation device 2 will be filled with a fibrous scaffolding 12made of a plurality of fibers (e.g. a yarn or a tow).

The fibrous scaffolding 12 is made from biocompatible fibers, preferablytextured fibers which provide a much lower bulk density filling thannon-texturized fiber. The low bulk density of textured fibers enablesrapid population of the immune modulation device 2 with significantnumbers of cells and helps to retain the fibrous scaffolding 12 withinthe shell 4. The fibrous scaffolding 12 is loaded with single or,multiple antigens and optionally other biologically active orpharmaceutically active compounds (e.g. cytokines (e.g. interlukins1-18; interferons α, β, and γ; growth factors; colony stimulatingfactors, chemokines, tumor necrosis factor α and β, etc.), non-cytokineleukocyte chemotactic agents (e.g. C5a, LTB₄, etc.), attachment factors,genes, peptides, proteins, nucleotides, carbohydrates or syntheticmolecules) or cells depending on the application.

The shell 4 and the fibrous scaffolding 12 of the device will be madewith a biocompatible material that may be absorbable or non-absorbable.The device will preferably be made from biocompatible materials that areflexible and thereby minimizing irritation to the patient. Preferablythe shell will be made from polymers or polymer blends having glasstransition temperature below physiologic temperature. Alternatively thedevice can be made with a polymer blended with a plasticizer that makesit flexible.

In theory but in no way limiting the scope of this invention it issuspected that the shell allows cell ingress and egress but hindersdiffusion of soluble molecules out of the device. This is believed tohelp to concentrate cytokines secreted by cells that have entered thedevice in response to loaded antigens (e.g. antigen presenting cells)and other cells (e.g. helper T cells, B cells etc.) which are present inthe device. The fibrous scaffolding provides a scaffold for cells toreside on and process the antigens. This local concentration of cellsand cytokines significantly enhances the immune response relative toimplantation of antigens with standard adjuvants.

The intended recipient of the implantable device is an animal;preferably a human, but also including livestock animal, (e.g. sheep,cow, horse, pig, goat, lama, emu, ostrich or donkey), poultry (e.g.chicken, turkey, goose, duck, or game bird), fish (e.g. salmon orstrugeon), laboratory animal (e.g. rabbit, guinea pig, rat or mouse)companion animal (e.g. dog or cat) or a wild animal in captive or freestate.

Numerous biocompatible absorbable and nonabsorbable materials can beused to make the shell or fibrous scaffolding. Suitable nonabsorbablematerials for use in as the shell or fibrous scaffolding include, butare not limited to, polyamides (e.g. polyhexamethylene adipamide (nylon6,6), polyhexamethylene sebacamide (nylon 610), polycapramide (nylon 6),polydodecanamide (nylon 12) and polyhexamethylene isophthalamide (nylon6I), copolymers and blends thereof), polyesters (e.g. polyethyleneterephthalate, polybutyl terphthalate (e.g. as described in EPA 287,899and EPA 448,840), copolymers (e.g. as described in U.S. Pat. No.4,314,561; Re 32,770; U.S. Pat. Nos. 4,224,946; 5,102,419 and 5,147,382)and blends thereof), fluoropolymers (e.g. polytetrafluoroethylene andpolyvinylidene fluoride copolymers (e.g. as described in U.S. Pat. No.4,564,013) and blends thereof), polyolefins (e.g. polypropyleneincluding atactic but preferably isotactic and syndiotacticpolypropylene and blends thereof, as well as, blends composedpredominately of isotactic or syndiotactic polypropylene blended withheterotactic polypropylene and polyethylene), organosiloxanes (e.g.polydimethylsiloxane rubber such as SILASTIC® silicone tubing from DowCorning), polyvinyl resins (e.g. polystyrene, polyvinylpyrrolidone,etc.) and blends thereof.

Additionally the fibrous scaffolding may be made from natural fiberssuch as cotton, linen and silk (although silk is referred to as anonabsorbable material, it is broken down in the human body). Raw silkconsists of two filaments that are held together by seracin (silk glue).The silk is degummed (the seracin is removed) and the resulting singlefilaments are used to manufacture the fiber. The denier per filament(dpf) of individual silk fibers will range from about 0.8 to about 2.0.For fiber manufacture it is common to used silk with a dpf of from about0.8 to about 1.6 and more preferably a dpf of from about 0.8 to about1.4. The best grades of silk are easily obtainable from suppliers inChina and Japan.

Polyesters are also well known commercially available synthetic polymersthat may be used to make the shell or fibrous scaffolding. The mostpreferred polyester for making this device is polyethyleneterephthalate. Generally, polyethylene terephthalate polymers used tomake fibers will have a weight average molecular weight of greater than30,000 preferably greater than 40,000 and most preferably in the rangeof from about 42,000 to about 45,000. The filaments formed from thesepolymers should have a tenacity of greater than 5 grams/denier andpreferably greater than 7 grams/denier. Polyethylene terephthalate yarnsare commonly available from a variety of commercial fiber suppliers(such as E.I. DuPont and Hoechst Celanese). Preferred are commerciallyavailable fibers that may be purchased from Hoechst Celanese under thetrademark TREVIRA® High Tenacity type 712 and 787 polyester yarns.

A variety of fluoropolymers may also be used to make the shell and thefibrous scaffolding such as polytetrafluoroethylene and polyvinylidenefluoride (i.e. as in U.S. Pat. No. 4,052,550), copolymers and blendsthereof. Currently the preferred are the fluoro polymers blends ofpolyvinylidene fluoride homopolymer and polyvinylidene fluoride andhexafluoropropylene copolymer which is described in U.S. Pat. No.4,564,013 hereby incorporated by reference herein.

As previously stated the term polypropylene for the purposes of thisapplication include atactic but will be preferably isotactic andsyndiotactic polypropylene (such as is described in U.S. Pat. No.5,269,807 hereby incorporated by reference herein) and blends thereof,as well as, blends composed predominantly of isotactic or syndiotacticpolypropylene blended with heterotactic polypropylene and polyethylene(such as is described in U.S. Pat. No. 4,557,264 issued Dec. 10, 1985assigned to Ethicon, Inc. hereby incorporated by reference) andcopolymers composed predominantly of propylene and other alpha-olefinssuch as ethylene (which is described in U.S. Pat. No. 4,520,822 issuedJun. 4, 1985 assigned to Ethicon, hereby incorporated by reference). Thepreferred polypropylene material for making fibers is isotacticpolypropylene without any other polymers blended or monomerscopolymerized therein. The preferred method for preparing the flexiblepolypropylene fibers of the present invention utilizes as the rawmaterial pellets of isotactic polypropylene homopolymer having a weightaverage molecular weight of from about 260,00 to about 420,000.Polypropylene of the desired grade is commercially available in bothpowder and pellet form.

A variety of bioabsorbable polymers can be used to make the shell orfibrous scaffolding of the present invention. Examples of suitablebiocompatible, bioabsorbable polymers include but are not limited topolymers selected from the group consisting of aliphatic polyesters,poly(amino acids), copoly(ether-esters), polyalkylenes oxalates,polyamides, tyrosine derived polycarbonates, poly(iminocarbonates),polyorthoesters, polyoxaesters, polyamidoesters, polyoxaesterscontaining amine groups, poly(anhydrides), polyphosphazenes,biomolecules (i.e., biopolymers such as collagen, elastin, bioabsorbablestarches, etc.) and blends thereof. For the purpose of this inventionaliphatic polyesters include, but are not limited to, homopolymers andcopolymers of lactide (which includes lactic acid, D-, L- and mesolactide), glycolide (including glycolic acid), ε-caprolactone,p-dioxanone (1,4-dioxan-2-one), trimethylene carbonate(1,3-dioxan-2-one), alkyl derivatives of trimethylene carbonate,delta-valerolactone, beta-butyrolactone, gamma-butyrolactone,ε-decalactone, hydroxybutyrate, hydroxyvalerate, 1,4-dioxepan-2-one(including its dimer 1,5,8,12-tetraoxacyclotetradecane-7,14-dione),1,5-dioxepan-2-one, 6,6-dimethyl-1,4-dioxan-2-one, 2,5-diketomorpholine,pivalolactone, gamma, gamma-diethylpropiolactone, ethylene carbonate,ethylene oxalate, 3-methyl-1,4-dioxane-2,5-dione,3,3-diethyl-1,4-dioxan-2,5-dione, 6,8-dioxabicycloctane-7-one andpolymer blends thereof. Poly(iminocarbonates), for the purpose of thisinvention, are understood to include those polymers as described byKemnitzer and Kohn, in the Handbook of Biodegradable Polymers, edited byDomb, et. al., Hardwood Academic Press, pp. 251-272 (1997).Copoly(ether-esters), for the purpose of this invention, are understoodto include those copolyester-ethers as described in the Journal ofBiomaterials Research, Vol. 22, pages 993-1009, 1988 by Cohn and Younes,and in Polymer Preprints (ACS Division of Polymer Chemistry), Vol.30(1), page 498, 1989 by Cohn (e.g. PEO/PLA). Polyalkylene oxalates, forthe purpose of this invention, include those described in U.S. Pat. Nos.4,208,511; 4,141,087; 4,130,639; 4,140,678; 4,105,034; and 4,205,399hereby incorporated by reference herein. Polyphosphazenes, co-, ter- andhigher order mixed monomer-based polymers made from L-lactide, D,L-lactide, lactic acid, glycolide, glycolic acid, para-dioxanone,trimethylene carbonate and epsilon-caprolactone such as are described byAllcock in The Encyclopedia of Polymer Science, Vol. 13, pages 31-41,Wiley Intersciences, John Wiley & Sons, 1988 and by Vandorpe, et al inthe Handbook of Biodegradable Polymers, edited by Domb, et al, HardwoodAcademic Press, pp. 161-182 (1997). Polyanhydrides include those derivedfrom diacids of the form HOOC—C₆H₄—O—(CH₂)_(m)—O—C₆H₄—COOH, where m isan integer in the range of from 2 to 8, and copolymers thereof withaliphatic alpha-omega diacids of up to 12 carbons. Polyoxaesters,polyoxaamides and polyoxaesters containing amines and/or amido groupsare described in one or more of the following U.S. Pat. Nos. 5,464,929;5,595,751; 5,597,579; 5,607,687; 5,618,552; 5,620,698; 5,645,850;5,648,088; 5,698,213; 5,700,583; and 5,859,150 hereby incorporatedherein by reference. Polyorthoesters such as those described by Hellerin Handbook of Biodegradable Polymers, edited by Domb, et al, HardwoodAcademic Press, pp. 99-118 (1997).

As used herein, the term “glycolide” is understood to includepolyglycolic acid. Further, the term “lactide” is understood to includeL-lactide, D-lactide, blends thereof, and lactic acid polymers andcopolymers.

Particularly well suited for use in the present invention arebiocompatible absorbable polymers selected from the group consisting ofaliphatic polyesters, copolymers and blends which include but are notlimited to homopolymers and copolymers of lactide (which includes D-,L-, lactic acid and D-, L- and meso lactide), glycolide (includingglycolic acid), epsilon-caprolactone, p-dioxanone (1,4-dioxan-2-onewhich is described in U.S. Pat. No. 4,052,988 incorporated herein byreference herein), alkyl substituted derivatives of p-dioxanone (i.e.6,6-dimethyl-1,4-dioxan-2-one which is described in U.S. Pat. No.5,703,200 assigned to Ethicon and hereby incorporated by reference),trimethylene carbonate (1,3-dioxan-2-one), alkyl substituted derivativesof 1,3-dioxanone (which are described in U.S. Pat. No. 5,412,068incorporated herein by reference), delta-valerolactone,beta-butyrolactone, gamma-butyrolactone, epsilon-decalactone,hydroxybutyrate, hydroxyvalerate, 1,4-dioxepan-2-one (described in U.S.Pat. No. 4,052,988 and its dimer1,5,8,12-tetraoxacyclotetradecane-7,14-dione which is described in U.S.Pat. No. 5,442,032 assigned to Ethicon and hereby incorporated herein byreference), 1,5-dioxepan-2-one, and polymer blends thereof. Preferredfiber materials include but are not limited to copolymers oftrimethylene carbonate, epsilon-caprolactone and glycolide (such as aredescribed in U.S. Pat. Nos. 5,431,679 and 5,854,383 hereby hereinincorporated by reference) and copolymers of p-dioxanone, trimethylenecarbonate and glycolide and copolymers of lactide and p-dioxanone.Preferred are fibers made from lactide and glycolide sometimes referredto herein as simply homopolymers and copolymers of lactide and glycolideand copolymers of glycolide and epsilon-caprolactone i.e. as describedin U.S. Pat. Nos. 5,133,739; 4,700,704 and 4,605,730 incorporated hereinby reference), most preferred for use as a fiber is a copolymer that isfrom about 80 weight percent to about 100 weight percent glycolide withthe remainder being lactide. More preferred are copolymers of from about85 to about 95 weight percent glycolide with the remainder beinglactide.

The molecular weight of the polymers used in the present invention canbe varied as is well know in the art to provide the desired performancecharacteristics. However, it is preferred to have aliphatic polyestershaving a molecular weight that provides an inherent viscosity betweenabout 0.5 to about 5.0 deciliters per gram (dl/g) as measured in a 0.1g/dl solution of hexafluoroisopropanol at 25° C., and preferably betweenabout 0.7 and 3.5 deciliters per gram (dl/g).

As mentioned above, the outer surface 8 of shell 4 will be perforatedwith pores 6, which provide a passageway for the ingress and egress ofcells to the interior lumen 10 of the immune modulation device 2. At thetime of implantation the shell 2, is substantially impermeable todiffusion of water through the non-perforated walls of the shell. Theshell 2 is preferably made from one or more absorbable polymers that maybecome more permeable to aqueous media as they degrade. Absorbablepolymers can either be of natural or synthetic origin. The absorbablepolymers for the membrane most preferably have a glass transitiontemperature below physiologic temperature and would therefore be lessirritating when implanted in soft tissues. Preferred polymers for theshell would include copolymers with a significant content (at least 30weight percent) of epsilon-caprolactone or para-dioxanone. Aparticularly desirable composition includes an elastomeric copolymer offrom about 35 to about 45 weight percent epsilon-caprolactone and fromabout 55 to about 65 weight percent glycolide, lactide (or lactic acid)and mixtures thereof. Another particularly desirable compositionincludes para-dioxanone homopolymer or copolymers containing from about0 to about 80 weight percent para-dioxanone and from about 0 to about 20weight percent of either lactide, glycolide and combinations thereof.The degradation time for the membrane in-vivo is preferably longer than1 month but is shorter than 6 months and more preferably is longer than1 month but less than 4 months.

The shell 4 can be of any shape into which the fibrous scaffolding canbe placed. The shell can initially have openings that may be latersealed following placement of the fibrous scaffolding 12. The shell 4can be made by conventional polymer processing techniques includingmolding, welding, casting, extrusion, injection molding, machiningprocess or combinations thereof. These conventional procedures are wellknown in the art and described in the Encyclopedia of Polymer Scienceand Engineering, incorporated herein as reference. Melt extrusion is thepreferred method of process as it is rapid, inexpensive, scalable, andcan be performed solvent-free for many polymers of interest. Processingaides and plasticizers can be added to the polymer to decrease theprocessing temperature and/or modify the physical properties of theconstruct. Processing aides, such as solvents, can be added to decreasethe processing temperature by decreasing the glass transitiontemperature of the polymer. Subsequently, the aide can be removed byeither heat and/or vacuum or by passing the extruded construct through asecondary solvent in which the polymer has minimal solubility but ismiscible with the processing aide. For example halogenated solvents suchas methylene chloride or chloroform can be added to homo- and copolymersof lactide and epsilon-caprolactone. After extrusion, the solvent can beremoved through evaporation, vacuum, and/or heat. These solvents couldalso be extracted by passing the extrudate through a secondary solventsuch as alcohol, which has miscibility with the halogenated solvent.Plasticizers can also be incorporated into a polymer to increase itsworkability, flexibility, or distensibility. Typically these materialswork by increasing the free volume of the polymer. For example manycitrates, malates and caprilates will work to plasticize many aliphaticpolyesters. Oligomers of a given polymer or copolymer can also be usedto plasticize a system.

The preferred shapes of the shell are those with a minimal diameter inone dimension to facilitate placement using a small gauge needle. A mostpreferred shape is a cylinder with an outer diameter preferably lessthan 1 millimeter and most preferably less than 750 microns. This shapeand size facilitates implantation of the device using an 18 gauge needleor smaller. For this embodiment it is preferred that the wall thicknessis preferably less than 250 microns and most preferably is less than 150microns. The pores 6 in the shell 4 generally are large enough toprovide for the ingress and egress of cells. The pores are preferablylarger than about 10 microns but smaller than about 500 microns incross-sectional diameter and more preferably are from about 100 to about400 microns in cross-sectional diameter. The density of perforationspreferably does not exceed 25% of the outer surface area of the deviceand more preferably is below 10% of the outer surface area of the shellof the immune modulation device. The pores can be formed using anyappropriate drilling technique (e.g. using a hypodermic needle,mechanical or laser) or alternatively by including a solvent or watersoluble solid in the wall polymer which later can be leached out byimmersing the tube in the solvent to generate the hole. Alternatively,if biocompatible water soluble particles such as sugars, amino acids,polymers such as PVP, proteins such as gelatin, carbohydrates such ashyalyronic acid and certain carboxy methylcelluloses are used, thedevice can be implanted with the particles present. Upon exposure tobody fluids the pore forming particles can leach out or degrade formingpores. Most of the pore must extend completely through the wall of thedevice and provide a pathway for cells involved in the immune responseto ingress into the interior lumen 10 of the device as well as forantigen and cytokines to diffuse out of the interior lumen 10 of theimmune modulation device 2. If the immune modulation device 2 has one ormore open ends 14 of the immune modulation device can either be sealedwith layer 16 or left open, but are preferably left open. One embodimentof an immune modulation device with one sealed end is illustrated inFIG. 3.

In another embodiment of the present invention two portions of theinterior surface 18 may contact the fibrous scaffolding 12 to restrainmovement of the fibers in the immune modulation device 2. For example ifthe immune modulation device 2 were cylindrical a portion of the devicecould be crimped about the fibrous scaffolding 12. The crimping could beperformed with heating to permanently reshape a portion of the shell 4.One embodiment of a crimped device is illustrated in FIG. 4.Alternatively, the crimping could be performed with cutting and sealingone end of the immune modulation device 2 to form a cylindrical devicewith one sealed end 20. One embodiment of this device with a sealed endis illustrated in FIG. 5.

Fibers suitable for use in the present device can be made usingconventional spinning processes such as melt spinning processes orsolution spinning. After spinning the yarns may be quenched, treatedwith a spin finish, drawn and annealed as is known in the art. Thefibrous scaffolding made from these fibers should have a porosity ofgreater than 20%, more preferably from about 25% to about 95%, and mostpreferably from about 30% to about 90% to the fibers.

The fibrous scaffold should be made up of filaments having a denier inthe range of from about 0.2 to about 10 and preferably a denier fromabout 0.8 to about 6 and more preferably a denier of from about 1 toabout 3. The filaments are commonly extruded in bundles (yarns) having adenier in the range of from about 20 to about 400 denier and preferablyabout 50 to about 100 denier. The fibers need to be treated to developthe bulk density or porosity need for a fibrous scaffold. The preferredyarns for this application are textured yarns. There are many forms oftextured yarns that may be used to form a fibrous scaffolding such asbulked yarns, coil yarns, core bulked yarns, crinkle yarns, entangledyarns, modified stretch yarns, nontorqued yarns, set yarns, stretchyarns and torqued yarns and combinations thereof. Methods for makingthese yarns are well known and include the false-twisted method,entanglement (e.g. rotoset or air jet entangled), crimping (e.g. gearcrimped, edge crimped or stuffer box crimped), and knit-de-knit.Preferably the fibers will be textured by false-twisting method, thestuffer box method or knit-de-knit method of textile texturing. Thefilaments are texturized to provide a high degree of permanent crimpingor random looping or coiling. Crimped fibers are currently preferred.Crimping causes the orientation of the filament to change angle at thecrimping points. The angle change is preferably greater than 10 degreesat each crimp point. The crimping can be accomplished through a varietyof processes but is most easily generated by feeding the extrudedfilaments through a stuffer box.

The fibrous scaffolding is preferably a texturized fiber made from anabsorbable polymer that can either be of natural or synthetic origin.Each fiber filament preferably has a diameter of less than 20 micronsand most preferably less than 15 microns. This imparts to the filamentssufficient flexibility to completely fill the lumen of the tube andprovide a suitable surface for cells to colonize in the lumen of theshell. The fibers preferably will take longer than 1 month to biodegrade(via hydrolysis and/or enzymatic activity) in a normal subcutaneousimplantation but will completely be biodegraded within 6 months and morepreferably between 1 and 4 months. An example of a good polymer formaking a fibrous scaffolding is a copolymer of 90% glycolide (orglycolic acid) and 10% lactide (or lactic acid) having an inherentviscosity between about 0.7 to about 1.5 deciliters per gram (dl/g) asmeasured in a 0.1 g/dl solution of hexafluoroisopropanol at 25° C.

The most significant advantage with the use of fibrous scaffolding isthat the fibers can be easily placed within the shell. For example, atextured fiber can be stretched and then the shell extruded, molded orotherwise coated of shaped around them. Following placement of the shellaround the stretched fibers, the tension can be relaxed which allows thefibers to assume their crimped shapes and fill the space inside theshell. Unlike sponges that can also be compressed, the textured fiberscan be wound onto spools in very long lengths, which can be continuouslyfed as a core in a core-sheath or wire coating extrusion process. Thesheath can be a molten polymer that is co-extruded and drawn with thestretched fibers. Individual units could be created by cutting the coresheath constructs to a desired length. Perforations can be created bypiercing the tubing wall to form small holes. Open pore sponges are verydifficult to produce in a continuous form and hence would require theshell be formed as small discrete units into which the sponge can bestuffed.

An additional advantage of fibrous scaffolding over sponges inprocessing is that the spool of fibers will be strong while an open cellsponge will be weak and will tear easily. This is an importantconsideration in miniaturization of the device. Small bunches of fiberscan be stretched, compressed or otherwise exposed to robust mechanicalprocessing. In contrast, small dimension sponges tear or break easilyand can only be subjected to gentle processing. Formation ofsub-millimeter devices necessarily subjects the filling to significantstresses in order to fit within the small dimensions of the shell.Miniaturization is very important in minimizing patient pain anddiscomfort following implantation of the device. Hence the use offibers, which can be compressed more substantially that an open-cellsponge, enables a smaller device which is preferable from the patient'sstandpoint.

At first glance it may appear desirable to fill the shell with simplestraight fibers. However, straight fibers would settle and bunch in theshell over time and would not provide a hospitable environment foringress of large numbers of cells. Additionally, straight fiber wouldrequire that the device be modified to prevent the fibers from fall outof the device during handling. If the fibers were densely packed orbraided so as to provide an interference fit in the shell there wouldnot be sufficient porosity for cell colonization. Texturizing the fibersallows them to effectively fill space while maintaining porositiesneeded for colonization with high cell number densities. This low bulkdensity property of the texturized fibers enables an interference fitwith the walls of the shell without having to worry about compaction ofthe filling during storage and handling.

The textured fibers can either be filled into a preformed tube or thetube can be extruded around the filaments. During the filling process itmay be desirable to stretch the filaments to a straight orientation.This radially compresses the fibers to a much smaller diameter than theyoccupy when in a relaxed state. The void volume in the lumen of the tubeis preferably greater than 30% and more preferably greater than 50%.Once relaxed the textured filaments should completely fill the lumen ofthe device and should stay in place in the lumen due to the compressiveforce exerted by the tubing walls on the filling.

A preferred process for generating the textured fiber filled tubesconsists of extruding the tubing around the stretched filaments in acontinuous manner. This can be accomplished by having the textured fiberwound on a spool and fed under tension through the lumen of an extruderdie as a core around which a sheath of wall polymer is continuouslyextruded. Perforations can later be drilled through the wall of thepolymer either mechanically or using electromagnetic radiation (e.g.laser ablation). It is especially desirable to adjust the depth ofdrilling so that the wall is completely punctured but the filling is notdamaged. With electromagnetic radiation this can be accomplished byprovided just enough focused energy to ablate through the wall of thetube. Alternatively it is possible to fill a preformed tube by tying thetextured fiber to a thin wire or needle and then dragging the texturedfilaments under tension through the tubing. Additionally, it is possibleto fill a preformed tube by using a pressure differential (e.g. vacuumor blown air) to pull the textured filament through the tubing. In thisconfiguration the perforations in the tube can be created either pre orpost filling of the lumen. The length of the textured fiber filled tubeis cut to be greater than a few millimeters and more preferably greaterthan 5 millimeters.

The lumen of the device is filled with an antigen, mixture of antigensand optionally one or more cytokines, prior to implantation. The antigencan either be in a dry or wet form. Potential antigens include peptides,proteins, nucleotides, carbohydrates or even cells or cell fragments.The antigen or antigens can be bioavailable at the time of implantation(for immediate release with optionally a portion in a sustained releaseform) or designed to be bioavailable after implantation (e.g. 3 daysafter). The antigen or antigens can be supplied in a sustained releaseform, such as encapsulated in microparticles, can be supplied in a nakedform or in combinations thereof. One method by which antigen can beloaded is to suspend it in a suitable liquid which is then injected orpumped into the lumen of the filled tube. The textured fiber fillingmust be under sufficient compression as to stay in place through theconvection of the fluid. The fluid filled device can then be implantedor the filling fluid can be dehydrated or lyophilized prior toimplantation leaving behind in the lumen of the filled device thedesired antigen or antigens. Alternatively the textured fiber may beimpregnated with the antigen etc. prior to insertion into the shell. Thedehydrated system will rehydrate following implantation that willpresent the antigen in a suitable form for generating the desiredimmunomodulatory response. A particularly convenient site ofimplantation is subcutaneous insertion directly beneath the skin,however any site which offers access to antigen presenting cells,macrophages and other cells of the immune system is acceptable. Desiredimmunomodulatory responses can include either generation of humoraland/or cellular immunity against the desired antigen or alternativelydesensitization towards particular allergen or cell types.

Any specific antigen or combination of synthetic or natural antigens maybe employed as the antigenic substance for incorporation in the immunemodulation device and subsequent implantation in the animal. Theantigens can be from bacterial, fungal, viral, cellular (e.g. fromparasites or in autoimmune treatments from animal tissue) or syntheticsources which contain at least one epitope to which the immune system ofthe animal will respond. In immunization the antigen is desired toinduce protective immunity to the animal to which it is administered.The antigen source can be preparations of killed microorganisms; livingweakened microorganisms; inactivated bacterial toxins (toxoids);purified macromolecules; recombinantly produced macromolecules and thelike. Preferably for mammals, the antigen or mixtures of antigens willbe derived from bacterial or viral sources with polyvalent antigenicdomains being present. Suitable bacterial antigen sources include, butare not limited to, Actinobacillus equuli, Actinobacillus lignieresi,Actinobaccilus seminis, Aerobacter aerogenes, Borrelia burgdorferi,Borrelia garinii, Borrelia afzelii, Babesia microti, Klebsiellapneumoniae, Bacillus cereus, Bacillus anthracis, Bordetella pertussis,Brucella abortus, Brucella melitensis, Brucella ovis, Brucella suis,Brucella canis, Campylobacter fetus, Campylobacter fetus intestinalis,Chlamydia psittaci, Chlamydia trachomatis, Clostridium tetani,Corynebacterium acne Types 1 and 2, Corynebacterium diphtheriae,Corynebacterium equi, Corynebacterium pyogenes, Corynebacterium renale,Coxiella burnetii, Diplococcus pneumoniae, Escherichia coli, Ehrlichiaphagocytophila, Ehrlichia equi, Francisella tularensis, Fusobacteriumnecrophorum, Giardia lambia, Granuloma inguinale, Haemophilusinfluenzae, Haemophilus vaginalis, Group b Hemophilus ducreyi,Lymphopathia venereum, Leptospira pomona, Listeria monocytogenes,Microplasma hominis, Moraxella bovis, Mycobacterium tuberculosis,Mycobacterium laprae, Mycoplasma bovigenitalium, Neisseria gonorrhea,Neisseria meningitidis, Pseudomonas maltophiia, Pasteurella multocida,Pasteurella hamemolytica, Proteus vulgaris, Pseudomonas aeruginosa,Plasmodium berghei, Plasmodium falciparum, Plasmodium malariae,Plasmodium ovale, Plasmodium vivax, Rickettsia prowazekii, Rickettsiamooseri, Rickettsia rickettsii, Rickettsia tsutsugamushi, Rickettsiaakari, Salmonella abortus ovis, Salmonella abortus equi, Salmonelladublin, Salmonella enteritidis, Salmonella heidleberg, Salmonellaparatyphi, Salmonella typhimurium, Shigella dysenteriae, Staphylococcusaureus, Streptococcus ecoli, Staphylococcus epidermidis, Streptococcuspyrogenes, Streptococcus mutans, Streptococcus Group B, Streptococcusbovis, Streptococcus dysgalactiae, Streptococcus equisimili,Streptococcus uberis, Streptococcus viridans, Treponema pallidum, Vibriocholerae, Yersina pesti, Yersinia enterocolitica and combinationsthereof. Suitable fungi antigen sources including, but are not limitedto, Aspergillus fumigatus, Blastomyces dermatitidis, Candida albicans,Crytococcus neoformans, Coccidioides immitis, Histoplasma capsulatum andcombinations thereof. Suitable viral antigen sources from viral sourcesinclude, but are not limited to, influenza, HIV, hanta virus (e.g. SinNombre virus), Mumps virus, Rubella virus, Measles virus, Smallpoxvirus, Hepatitis virus, (e.g. A, B, C, D, E), Rift Valley Fever (i.e.Plebovirus), viral encephalitis, (e.g. Eastern equine encephaliticvirus, St. Louis encephalitic virus, Western equine encephalitic virus,West Nile Virus), human papilloma virus, cytomegalovirus, polio virus,rabies virus, Equine herpes virus, Equine arteritis virus, IBR—IBPvirus, BVD—MD virus, Herpes virus (humonis types 1 and 2) andcombinations thereof. Suitable parasite antigen sources include, but arenot limited to, Schistosoma, Onchocerca, parasitic amoebas andcombinations thereof. Preferred infectious diseases that this device andmethod may provide prophylaxis against include viruses such asinfluenza, HIV, human papilloma, hepatitis, cytomegalovirus, polio andrabies; bacteria for example E. coli, Pseudomonas, Shigella, Treponemapallidum, Mycobacterium (tuberculosis and laprae), Chlamydia,Rickettsiae, and Neisseria; fungi such as Aspergillus and Candida; andparasitic multicellular pathogens.

Suppression of the immune response may also be desirable to treatconditions, such as allergies, or to prepare patients for the exposureto foreign antigens, such as for transplant. Inappropriate immuneresponses are believed to be the underlying etiology in a number ofautoimmune and other diseases, such as type I diabetes, rheumatoidarthritis, multiple sclerosis, uveitis, systemic lupus erythematosus,myasthenia gravis, and Graves' disease. By implanting in an individual adevice of the present invention containing the suspect antigen, entry ofcells primed to recognize the antigen can be induced to undergoapoptosis, and be eliminated from the immune system. Elimination ofprogenitor antigen-specific cells can permit the later transplant offoreign antigens without rejection.

Further utilities of the present invention include improvements in thegeneration of polyclonal antibodies (immune serum) and nonclonalantibodies in laboratory animals and obtaining the desired isotype ofantibody so generated. In one embodiment, a procedure for preparingpolyclonal (immune serum) and monoclonal antibodies against an antigenavailable only in minute quantities can be performed by the device ofthe present invention. The device can be provided with a small amount ofthe rare antigen, in order to immunize the animal, after which spleencells can be harvested. This procedure offers an improvement overcurrent tedious and unpredictable method of introducing the rare antigendirectly into the spleen. Furthermore, the need for a boost immunizationmay be obviated by use of the device of the present invention, and, inaddition, an immune response will be generated more quickly. A shortenedtime required to immunize animals will allow the generation ofmonoclonal antibodes more rapidly. In another embodiment, immune cellsfor the production of hybridomas can be harvested from the device afterimmunization of an animal with an antigen provided within the device.This procedure can also be used to generate human monoclonal antibodies,by implanting a device of the present invention into an individual,loading the device with antigen, and then harvesting immune cells fromthe device for the production of hybridomas. The above-mentionedpolyclonal antibodies (immune serum) and monoclonal antibodies can beused for diagnosis, basic research, imaging and/or therapy. In anotherembodiment, human monoclonal antibodies can be generated using thedevice of the present invention implanted in a severe combinedimmunodeficiency (SCID) mouse, by the following procedure. First, humanperipheral blood lymphocytes are injected into a SCID mouse, wherein thehuman lymphocytes populate the murine immune system. After implantationof a device of the present invention comprising the desired antigenwhich is bioavailable after implantation, subsequent harvesting of cellsfrom the device will provide human B lymphocytes cells which can then beused to prepare hybridomas which secrete human antibodies against thedesired antigen.

A further utility of the device of the present invention is incollection of immune cells from a mammal for later reintroduction intothe mammal. Cells can be removed from the device, for example, byaspiration from the implanted device or collection from the device afterremoval from the body by dissolving the polymer matrix, subsequentstorage of the cells, for example by cryopreservation, andreintroduction into the mammal at a later time. This can be particularlyuseful for mammals undergoing whole body radiation therapy. A device ofthe present invention, without containing antigen, can be implanted andmaintained for a time sufficient to allow immune cells to migrate intothe device (e.g. seven to ten days). Subsequently the device or itscontents are removed and the cells contained therein cryopreserved.Following radiation therapy, the mammal can have the cells reintroducedinto the body, whereby the cells will reconstitute the immune system. Inanother embodiment of this utility, co-stimulatory factors such ascytokines which induce the proliferation of immune cells can beintroduced into the device to increase the yield of cells within thedevice, before harvesting. In a further embodiment, immune cellscollected from a device provided with antigen can be used for activeimmunization, wherein the cells can be stored and then reintroduced intothe mammal after, for example, a course of chemotherapy or othertherapeutic manipulation. In a still further embodiment, cells collectedfrom a device can be cyropreserved, and at a later time be exposed tothe antigen (for example, a cancer antigen) for ex-vivo propagation of Tcells prior to introduction into the body, for adoptive immunotherapy.

EXAMPLES

The following examples illustrate the construction of a textured fiberfilled device for generating an immunomodulatory response. Those skilledin the art will realize that these specific examples do not limit thescope of this invention and many alternative forms of an antigen loadedtextured fiber filled device could also be generated within the scope ofthis invention.

Example 1

Textured Fibrous Filling

Fiber texturing was performed using a Techtex® HDC10 texturizer(Techniservice, 738 West Cypress Street, Kennett Square, Pa.19348-0817). Nine spools of 56 denier natural 90/10 glycolide-co-lactide(IV of about 1.1 deciliters per gram (dl/g) as measured in a 0.1 g/dlsolution of hexafluoroisopropanol at 25° C. The filaments had been drawnabout 5× (original length compared to final length). The filaments wereplaced on the creel and combined into a single 504 denier tow by runningthe drawn yarns together through a common eyelet. The individual yarnfilament diameters were between 12-20 μm. A pretension of 5-7 grams wasused for each yarn by passing them through the gate tensioner. The largeyarn tow was then passed over a heated godet with the separator roller(15 wraps) with the heated godet being set to a temperature of 130° C.This yarn tow was then fed into the stuffer box by two crimper rolls.The clearance between the stuffer box and rollers was 0.012 inches andthe temperature in the stuffer box was about 50° C. (the box was notheated, the elevated temperature of 50° C. came from the yarn, heated onthe godet). Uniformity of crimp texture is maintained through accuratecontrol of the crimped column height in the stuffer box. The columnheight control is provided by the optical sensor located in the stufferbox and signaling the take up winder inverter to speed up/slow down. Thestuffer box optical sensor was set to hole no. 8 from the top of thebox. After the stuffer box, the textured yarn tow passed through thegate tensioner set at 5 grams for combining and keeping all yarns in thetow under the same tension. The crimped yarn then passed the overfeedrolls to reduce high yarn tension prior to winding on the take upwinder. The take up winder speed was set at 170 m/min. An image of theresulting textured fiber is shown in FIG. 2.

Example 2

Membrane Formation

Membranes were formed from both poly(para-dioxanone) (PDO) and acopolymer of 35/65 epsilon-caprolactone/glycolide (CAP/GLY). Theinherent viscosity (dl/g) of the PDO and CAP/GLY, as measured in a 0.1g/dl solution of hexafluoroisopropanol (HFIP) 25° C., were 1.80 and1.30, respectively. All membranes were formed by extrusion using a¾-inch Brabender single-screw extruder (C.W. Brabender® Instruments,Inc., So. Hackensack, N.J.) under flowing nitrogen. Membranes withseveral inner and outer dimensions were formed. Extrusion conditions forthe extruded membranes are shown in Table 1. Immediately following exitfrom the die, all membranes were run through a 12-foot cooling troughfilled with chilled water at a temperature of 5-10° C. For the CAP/GLYmembranes, short segments (˜2-3 ft.) were cut and hung from one end atroom temperature to allow solidification and crystallization of thepolymer.

TABLE 1 Extrusion conditions Die size Screw Take- Die × tip T_(zone1)T_(zone2) T_(zone3) T_(adapt.) T_(die) P_(block) P_(air) speed off OD IDPolymer (mil) (° C.) (° C.) (° C.) (° C.) (° C.) (psi) (psi) (rpm) (FTM)(mm) (mm) 35/65 170 × 138 140 145 145 145 140 1900 0.1 12  20 2.0 1.5CAP/GLY 35/65 102 × 83  140 145 145 145 145 4480 0 4 18 1.03 0.83CAP/GLY 35/65 53 × 40 140 145 145 145 140 4300 0.1 3 14 0.9 0.7 CAP/GLY35/65 56 × 40 140 145 150 150 150 2470 0.3 4 34 0.65 0.45 CAP/GLY PDO102 × 83  130 135 135 135 135 5000 0 5 20 1.03 0.83 PDO 102 × 83  145150 150 150 150 3750 0 5 20 0.65 0.45

After extrusion, the membranes were cut to the desired length (2-2.5 cm)using a razor blade. Membrane perforations were formed at Resonetics,Inc. (Nashua, N.H.) using an excimer laser (Lambda-Physik EMG201MSCExcimer Laser) operating at a wavelength of 193 nm. The laser wascoupled to a Resonetics engineering workstation consisting of a maskprojection imaging beam delivery system and a three-axis (XYtheta)computerized motion control system. Hole sizes ranging between 100 and500 microns were formed through the membrane walls. Drilling parametersfor the different tubing are shown in Table 2.

TABLE 2 Laser drilling conditions Fluence Pulse rate ˜Etch rate PolymerOD/ID (mm/mm) (J/cm²) (Hz) (μm/pulse) 35/65 CAP/GLY   2.0 × 1.5., 10 500.63 0.9 × 0.7 35/65 CAP/GLY 2.0 × 1.5 3.5 50 0.56 35/65 CAP/GLY 2.0 ×1.5 0.7 10 0.5 35/65 CAP/GLY  1.03 × 0.83, 2 25 0.67 0.65 × 0.45 PDO 1.03 × 0.83, 2.6 50 0.5 0.65 × 0.45

Example 3

VLN Construct Formation

The textured fiber filling from Example 1 was placed inside themembranes discussed in Example 2 as follows. Textured fiber was attachedto a small needle or thin filament of wire and pulled through themembrane. The fiber was cut to the length of the membrane. Availableporosity was calculated from the volume of the inner lumen of themembrane, weight of textured yarn placed inside of the membrane, and thedensity of the fibers used. Table 3 shows several of the constructgeometries and resultant porosities.

TABLE 3 Absorbable VLN constructs containing textured fiber. MembraneOD/ID/length Hole diameter # Fiber weight ˜Percent Composition(mm/mm/mm) (μm) holes (mg) porosity Sample # CAP/GLY 2.0/1.5/25 300 2012 80% 1 CAP/GLY 2.0/1.5/20 300 16 10 80% 2 CAP/GLY 2.0/1.5/20 300 12 1080% 3 CAP/GLY 2.0/1.5/20 300 8 10 80% 4 CAP/GLY 2.0/1.5/20 300 4 10 80%5 CAP/GLY 2.0/1.5/20 not applicable 0 10 80% 6 CAP/GLY 2.0/1.5/25 300 1610 83% 7 CAP/GLY 2.0/1.5/25 300 16 15 75% 8 CAP/GLY 2.0/1.5/20 300 20 883% 9 CAP/GLY 2.0/1.5/20 300 20 12 75% 10 CAP/GLY 0.65/0.45/25 150 4 265% 11 CAP/GLY 0.65/0.45/25 150 12 2 65% 12 CAP/GLY 0.65/0.45/25 150 202 65% 13 PDO 0.65/0.45/25 150 4 1.3 75% 14 PDO 0.65/0.45/25 150 8 1.375% 15 PDO 0.65/0.45/25 150 12 1.1 80% 16 PDO 0.65/0.45/25 150 16 1.375% 17

Example 4

Prior art (WO 99/44583) has demonstrated that a nonabsorbable deviceusing a 25 mm length of silicone tubing with an internal diameter of 1.5mm and outer diameter of 2 mm, fitted with a 25 mm-long segment ofhydroxylated polyvinyl acetate sponge induces a more robust immuneresponse to the influenza vaccine (in BALB/c mice) than traditionalintramuscular injections with and without the use of traditionaladjuvants such as Ribi. Similarly the device of the present inventionsuch as the absorbable, fiber-filled device described in Example 3(Sample #1) could be loaded with ˜100 ng of influenza antigen(FLUSHIELD® influenza virus vaccine, trivalent, Types A & B; obtainedfrom Henry Schein®, Melville N.Y.). Female BALB/c mice (6-8 weeks old)would be anesthetized with Avertin. One device per animal could beinserted through a 0.5-cm dorsal midline incision on day 1.

At appropriate intervals post-immunization the mice could be bled andthe sera tested for influenza-specific humoral response, usingconventional ELISA or other appropriate protocols to determine immuneresponse. The optimum dosage of antigen of the device could bedetermined by developing dose response curves at appropriate timeintervals post implantation. Similarly, the cell population in thedevice could be determined at appropriate intervals (e.g. days 3, 7, 10etc.) to verify the migration of cells into the device, cell types inthe device and optimum configuration of holes etc. to provide the mostadvantageous conditions for immune modulation in any animal with aparticular antigen (or antigens).

1. An immune modulation device that is suitable for use in modulating animmune response in animals, comprising: an impermeable biocompatibleshell having an outer surface comprising a plurality of pores ofsuitable size to allow the ingress and egress of immune cells, saidimpermeable biocompatible shell having an interior lumen, abiocompatible fibrous scaffolding being disposed within said interiorlumen, said fibrous scaffolding comprising textured yarn containingcrimped fibers having crimp points, wherein the orientation of filamentsin said crimped fiber changes angle at said crimp points; and an antigendisposed within said interior lumen.
 2. The immune modulation device ofclaim 1 wherein the fibrous scaffolding has a porosity of from about 25percent to about 95 percent.
 3. The immune modulation device of claim 1wherein the fibrous scaffolding is made from filaments with a diameterof less than 20 microns.
 4. The immune modulation device of claim 1wherein the fibrous scaffolding is made from filaments with a denier offrom about 0.2 to about
 10. 5. The immune modulation device of claim 1wherein the fibrous scaffolding is made from filaments with a denier offrom about 0.8 to about
 6. 6. The immune modulation device of claim 1wherein the fibrous scaffolding is made from a bundle of filamentshaving a total denier of from about 20 to about 400 denier.
 7. Theimmune modulation device of claim 1 wherein the textured yarn isselected from the group consisting of bulked yarns, coil yarns, corebulked yarns, crinkle yarns, entangled yarns, modified stretch yarns,nontorqued yarns, set yarns, stretch yarns, torqued yarns, andcombinations thereof.
 8. The immune modulation device of claim 1 whereinthe immune modulation device has a three dimensional shape selected fromthe group consisting of spherical, cylindrical, rectangular, andrhomboidal.
 9. The immune modulation device of claim 7 wherein theimmune modulation device is cylindrical in shape.
 10. The immunemodulation device of claim 9 wherein the cylindrically shaped immunemodulation device has an outer diameter of less than 1 millimeter. 11.The immune modulation device of claim 10 wherein the cylindricallyshaped immune modulation device has an outer diameter of less than 750microns.
 12. The immune modulation device of claim 9 wherein thecylindrically shaped immune modulation device has a wall thickness ofless than 250 microns.
 13. The immune modulation device of claim 12wherein the cylindrically shaped immune modulation device has a wallthickness of less than 150 microns.
 14. The immune modulation device ofclaim 1 wherein the pores on the outer surface of the immune modulationdevice comprise less than 25 percent of the outer surface.
 15. Theimmune modulation device of claim 14 wherein the pores range in sizefrom about 10 to about 500 microns.
 16. The immune modulation device ofclaim 1 wherein the immune modulation device is bioabsorbable.
 17. Theimmune modulation device of claim 16 wherein each of the biocompatibleshell and the biocompatible scaffolding are independently made from apolymer selected from the group consisting of aliphatic polyesters,poly(amino acids), copoly(ether-esters), polyalkylenes oxalates,polyamides, tyrosine derived polycarbonates, poly(iminocarbonates),polyorthoesters, polyoxaester, polyamidoesters, polyoxaesters containingamine groups, poly(anhydrides), polyphosphazenes, biomolecules; andblends thereof.
 18. The immune modulation device of claim 17 whereinboth the biocompatible shell and the biocompatible scaffolding are madefrom an aliphatic polyester.
 19. The immune modulation device of claim18 wherein the aliphatic polyester is selected from the group consistingof homopolymers and copolymers of lactide, glycolide, ε-caprolactone,p-dioxanone, trimethylene carbonate, alkyl derivatives of trimethylenecarbonate, delta-valerolactone, beta-butyrolactone, gamma-butyrolactone,ε-decalactone, hydroxybutyrate, hydroxyvalerate, 1,4-dioxepan-2-one,1,5-dioxepan-2-one, 6,6-dimethyl-1,4-dioxan-2-one, 2,5-diketomorpholine,pivalolactone, gamma, gamma-diethylpropiolactone, ethylene carbonate,ethylene oxalate, 3-methyl-1,4-dioxane-2,5-dione,3,3-diethyl-1,4-dioxan-2,5-dione, 6,8-dioxabicycloctane-7-one, andpolymer blends thereof.
 20. The immune modulation device of claim 19wherein the shell is made from an aliphatic polyester selected from thegroup consisting of homopolymers and copolymers of lactide, glycolide,ε-caprolactone, p-dioxanone, trimethylene carbonate, alkyl derivativesof trimethylene carbonate, 1,4-dioxepan-2-one, 1,5-dioxepan-2-one,6,6-dimethyl-1,4-dioxan-2-one, and polymer blends thereof.
 21. Theimmune modulation device of claim 19 wherein the shell is made from analiphatic polyester selected from the group consisting ofpoly(p-dioxanone), glycolide-co-ε-caprolactone,glycolide-co-trimethylene carbonate, glycolide-co-1,5-dioxepan-2-one,6,6-dimethyl-1,4-dioxan-2-one, and blends thereof.
 22. The immunemodulation device of claim 1 wherein the biocompatible fibrousscaffolding is made from an aliphatic polyester selected from the groupconsisting of homopolymers and copolymers of lactide, glycolide,ε-caprolactone, p-dioxanone, trimethylene carbonate, alkyl derivativesof trimethylene carbonate, 1,4-dioxepan-2-one, 1,5-dioxepan-2-one,6,6-dimethyl-1,4-dioxan-2-one, and polymer blends thereof.
 23. Theimmune modulation device of claim 22 wherein the biocompatible fibrousscaffolding is made from an aliphatic polyester selected from the groupconsisting of polyglycolide, poly(p-dioxanone),glycolide-co-ε-caprolactone, glycolide-co-trimethylene carbonate, andglycolide-co-lactide.
 24. The immune modulation device of claim 1wherein the shell is made from poly(p-dioxanone) and the fibrousscaffolding is made from a copolymer of about 90 weight percentglycolide and about 10 weight percent lactide.
 25. The immune modulationdevice of claim 1 wherein the shell is made from a copolymer of fromabout 35 to about 45 weight percent epsilon-caprolactone and from about55 to about 65 weight percent glycolide and the fibrous scaffolding ismade from a copolymer of about 90 weight percent glycolide and about 10weight percent lactide.
 26. The immune modulation device of claim 1wherein the antigen is selected from the group of natural antigens,synthetic antigens and combinations thereof.
 27. The immune modulationdevice of claim 26 wherein the natural antigen is derived from a microbeselected from the group consisting of Actinobacillus equuli,Actinobacillus lignieresi, Actinobaccilus seminis, Aerobacter aerogenes,Borrelia burgdorferi, Borrelia garinii, Borrelia afzelii, Babesiamicroti, Klebsiella pneumoniae, Bacillus cereus, Bacillus anthracis,Bordetella pertussis, Brucella abortus, Brucella melitensis, Brucellaovis, Brucella suis, Brucella canis, Campylobacter fetus, Campylobacterfetus intestinalis, Chlamydia psittaci, Chlamydia trachomatis,Clostridium tetani, Corynebacterium acne Types 1 and 2, Corynebacteriumdiphtheriae, Corynebacterium equi, Corynebacterium pyogenes,Corynebacterium renale, Coxiella burnetii, Diplococcus pneumoniae,Escherichia coli, Ehrlichia phagocytophila, Ehrlichia equi, Francisellatularensis, Fusobacterium necrophorum, Giardia lambia, Granulomainguinale, Haemophilus influenzae, Haemophilus vaginalis, Group bHemophilus ducreyi, Lymphopathia venereum, Leptospira pomona, Listeriamonocytogenes, Microplasma hominis, Moraxella bovis, Mycobacteriumtuberculosis, Mycobacterium laprae, Mycoplasma bovigenitalium, Neisseriagonorrhea, Neisseria meningitidis, Pseudomonas maltophiia, Pasteurellamultocida, Pasteurella hamemolytica, Proteus vulgaris, Pseudomonasaeruginosa, Plasmodium berghei, Plasmodium falciparum, Plasmodiummalariae, Plasmodium ovale, Plasmodium vivax, Rickettsia prowazekii,Rickettsia mooseri, Rickettsia rickettsii, Rickettsia isutsugamushi,Rickettsia akari, Salmonella abortus ovis, Salmonella abortus equi,Salmonella dublin, Salmonella enteritidis, Salmonella heidleberg,Salmonella paratyphi, Salmonella typhimurium, Shigella dysenteriae,Staphylococcus aureus, Streptococcus ecoli, Staphylococcus epidermidis,Streptococcus pyrogenes, Streptococcus mutans, Streptococcus Group B,Streptococcus bovis, Streptococcus dysgalactiae, Streptococcusequisimili, Streptococcus uberis, Streptococcus viridans, Treponemapallidum, Vibrio cholerae, Yersina pesti, Yersinia enterocolitica,Aspergillus fumigatus, Blastomyces dermatitidis, Candida albicansCrytococcus neoformans, Coccidioides immitis, Histoplasma capsulatum,influenza viruses, HIV, hanta viruses, human papilloma virus,cytomegalovirus, polio virus, rabies virus, Equine herpes virus, Equinearteritis virus, IBR—IBP virus, BVD—MD virus, Herpes virus (humonistypes 1 and 2), Mumps virus, Rubella virus, Measles virus, Smallpoxvirus, Hepatitis viruses, Rift Valley Fever virus, viral encephalitises,Schistosoma, Onchocerca, parasitic amoebas, and combination thereof. 28.The immune modulation device of claim 1 wherein the impermeablebiocompatible shell having an outer surface and an interior lumen isformed by extruding a biocompatible polymer.
 29. The immune modulationdevice of claim 9 wherein the cylinder has a first end and a second end,said first end being sealed.
 30. The immune modulation device of claim 1wherein said orientation of said crimped filaments at said crimp pointschanges angle by at least 10 degrees.
 31. The immune modulation deviceof claim 1 comprising at least one opening other than said pores throughwhich said fibers may pass.
 32. The immune modulation device of claim 9wherein the cylinder has a first end and a second end, wherein at leastone of said first and second ends is open.